EP0384061A2 - Procédé et appareil pour l'ajustage sélectif de dimensions d'une bobine à haute fréquence pour l'imagerie par résonance magnétique - Google Patents

Procédé et appareil pour l'ajustage sélectif de dimensions d'une bobine à haute fréquence pour l'imagerie par résonance magnétique Download PDF

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Publication number
EP0384061A2
EP0384061A2 EP89309341A EP89309341A EP0384061A2 EP 0384061 A2 EP0384061 A2 EP 0384061A2 EP 89309341 A EP89309341 A EP 89309341A EP 89309341 A EP89309341 A EP 89309341A EP 0384061 A2 EP0384061 A2 EP 0384061A2
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EP
European Patent Office
Prior art keywords
coil
mri
bridge
tuning
inductive
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Granted
Application number
EP89309341A
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German (de)
English (en)
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EP0384061A3 (fr
EP0384061B1 (fr
Inventor
Joseph W. Carlson
Leon Kaufman
Peter A. Rothschild
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University of California
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University of California
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Publication of EP0384061A3 publication Critical patent/EP0384061A3/fr
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Publication of EP0384061B1 publication Critical patent/EP0384061B1/fr
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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
    • G01R33/32—Excitation or detection systems, e.g. using radio frequency signals
    • G01R33/34—Constructional details, e.g. resonators, specially adapted to MR
    • G01R33/34084—Constructional details, e.g. resonators, specially adapted to MR implantable coils or coils being geometrically adaptable to the sample, e.g. flexible coils or coils comprising mutually movable parts
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
    • G01R33/32—Excitation or detection systems, e.g. using radio frequency signals
    • G01R33/34—Constructional details, e.g. resonators, specially adapted to MR
    • G01R33/34046—Volume type coils, e.g. bird-cage coils; Quadrature bird-cage coils; Circularly polarised coils
    • G01R33/34053—Solenoid coils; Toroidal coils
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
    • G01R33/32—Excitation or detection systems, e.g. using radio frequency signals
    • G01R33/36—Electrical details, e.g. matching or coupling of the coil to the receiver
    • G01R33/3628—Tuning/matching of the transmit/receive coil

Definitions

  • This invention is generally related to the field of magnetic resonance imaging (MRI) using nuclear magnetic resonance (NMR) phenomena. It is particularly directed towards method and apparatus for realizing practical adjustably sized RF coils for use in MRI procedures.
  • MRI magnetic resonance imaging
  • NMR nuclear magnetic resonance
  • Magnetic resonance imaging is now in widespread commercial usage. Magnetic resonance spectroscopic imaging (MRSI) is also now emerging from the laboratory.
  • MRSI Magnetic resonance spectroscopic imaging
  • MRI magnetic resonance imaging
  • NMR nuclear magnetic resonance
  • Resultant NMR RF responses are detected as emanating from that same volume and subsequently are processed so as to produce spatial maps of NMR nuclei populations which appear as visual images representing cross-sections through the image volume.
  • Necessary RF signal coupling to/from the image volume is made via tuned RF coils spatially disposed about or substantially adjacent to the image volume. Sometimes a common coil structure is used for both RF signal transmission and reception. In other instances, separate dedicated RF coil structures are utilized for the transmit and receive phases, respectively of the MRI process.
  • the coil structure can be selectively opened at this joint area so as to permit admission of the patient anatomy and then closed about the anatomy making proper RF electrical connections for use in a subsequent MRI procedure (after which the joint is then again opened to permit easy egress of the patient anatomy).
  • the need for achieving high filling factors is especially useful, for example, with relatively low magnetic field MRI (having correspondingly lower NMR frequencies) and where so-called "surface" coils of the solenoidal type are used to wrap about the appropriate portion of the patient anatomy (e.g., abdomen, neck, etc.).
  • neck coils might take, for example, three turns while belt coils for imaging the abdomen may typically involve two turns.
  • such coils might have, for example, two microhenries of inductance for operation at 2.77 MHz with about 1600 picofarads of parallel RF tuning capacitance so as to achieve resonance at this frequency.
  • RF resonance tuning is achieved with only about 100 picofarads of variable capacitance range since this is the typical range of the typical varicap used for remote RF tuning. If additional varicaps are connected in parallel so as to achieve added tuning range, then the capacitance per volt of tuning control voltage quickly becomes too great for proper fine tuning control.
  • the overall inductance of the coil also must be within a similarly narrow range for proper resonance tuning (e.g., after the coil is loaded by insertion of the patient anatomy).
  • proper resonance tuning e.g., after the coil is loaded by insertion of the patient anatomy.
  • there is perhaps only about 100 picofarads of variable capacitance out of a total tuning capacitance of 1600 picofarads there is only about 6% variability -- implying that the total loaded coil inductance also can only have a range of about 6% for proper resonant tuning.
  • a head coil supplied by Picker MRI Inc. for its' MRI system includes a section which may be completely disconnected from other portions of the coil so as to permit easy entry of the head anatomy. It is then reconnected via a suitable RF plug connectors so as to effectively reassemble the coil about the patient's head. So far as presently known, it does not appear that such plug connected section is used to change the size of the basic coil structure in this arrangement.
  • the bridge element may include both inductive and capacitive impedance which collectively present a sufficiently low net added impedance (when the bridge element is additively connected into the joint area of the coil so as to increase its size) that the same RF tuning/impedance matching capacitance may be used to tune the loaded (and now expanded size) coil to resonance and matched impedance conditions.
  • the main coil structure preferably includes flexible portions so as to accommodate the bridge element(s) and thus change its size
  • the bridge elements(s) themselves preferably may be relatively more rigid and of a properly curved cross-section so as to help determine the final shape of the expanded coil structure when connected therewithin.
  • an RF receiver coil for use in an MRI system may include plural turns having respectively associated inductances L1, L2 and L3 collectively connected across a parallel tuning capacitance C p and through coupling capacitances C s (which may be balanced or unbalanced).
  • the purposes of the capacitance C p and the capacitances C s are to achieve RF resonance at a predetermined frequency (i.e., the NMR frequency for nuclei to be imaged within a magnetic field of given strength) and also to match the RF impedance to a suitable transmission line (e.g., for connection to the standard RF receiver of the MRI system).
  • a predetermined frequency i.e., the NMR frequency for nuclei to be imaged within a magnetic field of given strength
  • a suitable transmission line e.g., for connection to the standard RF receiver of the MRI system.
  • variable tuning capacitance C p may actually be realized as an electrically tuned varicap providing a fairly narrow predetermined tuning range for the RF receiver coil.
  • the main RF receiver coil 100 may include a plug-connectable joint area 102.
  • a plug-connected bridge element iu4 When a plug-connected bridge element iu4 is inserted into this joint area, it provides an adjustable size for the main RF receiver coil by including properly sized bridge conductors for each turn having associated inductance LB1, LB2, and LB3.
  • a properly sized capacitance C B is included serially in at least one of the bridge conductors so as to minimize the net inductive impedance added by the bridge element 104 when plug-connected within the joint area 102 of the main RF receiver coil.
  • the standard RF tuning and impedance matching circuit 106 may still be used to achieve proper RF resonance tuning.
  • FIGURE 3 A simplified electrical schematic diagram of the resultant circuit is depicted in FIGURE 3.
  • the bridge capacitor is sized so as to minimize if not totally eliminate the net inductance added by the bridge conductors inserted within the various turns of the coil.
  • the original or main coil inductance may typically be approximately 2 microhenries. With added bridge elements this might be increased to approximately 2.5 microhenries (without any capacitive components). With these parameter values, the capacitance C B should be approximately 6,600 picofarads so as to approximately cancel the added net inductance associated with the bridge conductors per se . In this manner, the total composite net inductance of the coil structure is left at approximately 2 microhenries even after the adjustable bridge element has been inserted (by suitable plug connectors within the joint area 102).
  • the exemplary embodiments utilize solenoidal RF receiver coils
  • the invention can be used with virtually any type of MRI RF coil (especially of the surface type) where adjustably sized segments can be utilized so as to permit better fits to variably sized anatomies.
  • Such features are, of course, of more importance for lower frequency operations (e.g., 2.77 MHz) where the limited tuning range of a typical varicap capacitance is an important factor.
  • higher frequencies e.g.,15 MHz
  • coils of higher inductance may be able to realize advantage from use of this invention.
  • FIGURE 4 An expanded size coil 100 already having bridge element 104 plug-connected in place is diagrammatically depicted at FIGURE 4 in place about a patient's neck anatomy.
  • the zero net inductance bridge may have a selected length X to similarly expand the coil size when plug-connected between the female and male connector portions 102A and 102B of joint area 102 (which connectors 102A and 102B may be matingly connected together for a "normal" smaller size patient).
  • the main RF receiver coil 100 includes conductive portions 200 formed on a flexible insulating substrate 202 (which may be photo-resist etched from a copper cladded insulating substrate in the manner of conventional printed circuit boards).
  • the male and female mating plug connectors 102B, 102A on the main coil structure 100 and connectors 204B, 204A on the bridge element may be of suitable conventional design.
  • the female connector may include a beryllium copper spring portions (e.g., of the type used on door connectors of RF screen rooms) while the male portion of the connector may be a simple extended portion of the printed circuit conductor of the turn (or an extender conductor element soldered or otherwise conductively affixed thereto).
  • the bridge element 104 may typically also be formed on an insulating substrate 206.
  • this substrate is of a more rigid material and is formed so as to include an appropriate curvature to help establish the proper shape of the flexible main coil 100 when the bridge element is connected within the Joint area 102.
  • FIGURE 6 A plan view of the bridge unit 104 is shown in FIGURE 6.
  • the bridge capacitance C B is shown schematically in FIGURE 6, but in reality may take the form of a small rectangular or circular element with tabs soldered across a conductivity break in the middle bridge conductor.
  • the capacitance is located so as to present a symmetrical, balanced, RF circuit.
  • a support stand 250 may be suitably shaped (e.g., to aid in proper neck or back support) and fixedly attached to the mid-portion of coil 100 so as to maintain it in a predetermined orientation.
  • This housing also may contain any necessary RF tuning impedance matching components.
  • a collection or "set" of bridges A, B, C having different respective lengths (and correspondingly different suitably sized capacitance) and relatively more rigid cross-sections of appropriate curvature may be associated with the coil apparatus so that an appropriate one of the bridges might be used to realize an appropriate final diameter for the composite coil structure in actual use.
  • FIGURE 8-12 An exemplary neck coil embodiment of this invention is depicted more particularly at FIGURE 8-12.
  • the joint portion 102 as shown as connected without a bridge connector so is to realize the minimum diameter coil 100.
  • suitable connections to RF MRI circuits and to tuning/matching control voltage conductors may be made via suitable cable connections with the base 250 (in which the tuning and matching circuits may be located).
  • the adaptor may be made of suitable dimensions (e.g., 3.5 inches long plus additional connector housing length) and made of relatively rigid structure having a slight bend to match the radius of curvature of the resulting composite coil.
  • three solenoidal turns are employed of 1/2 inch wide copper with approximately 1/4 inch spaces between the copper conductors of the turns at the lower portion disposed nearest the neck's spinal column members.
  • a suitable narrowing and shaping of the coil is effected as shown.
  • the center of these three bridge conductors contains a serially connected capacitance element (e.g., 6,000 picofarads) to minimize the added collective inductive reactance of the several bridge conductors.
  • the flexible circuit board used for the main neck coil has the configuration and size shown in FIGURE 11 for the presently preferred exemplary embodiment of neck coil.
  • Base 250 is similarly depicted in more detail at FIGURE 12.
  • the printed circuit board is fixedly mounted onto the base with suitable electrical connections being made from the coil at the lower portion of the turns directly into the base housing area.
  • the coil is suitably and conventionally connected to RF tuning/matching components.
  • the coil 100 has three turns so there will be three male "pins" on one side and three female plugs on the other side of the connector structure used in the joint area 102.
EP89309341A 1989-02-21 1989-09-14 Procédé et appareil pour l'ajustage sélectif de dimensions d'une bobine à haute fréquence pour l'imagerie par résonance magnétique Expired - Lifetime EP0384061B1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US312189 1989-02-21
US07/312,189 US4897604A (en) 1989-02-21 1989-02-21 Method and apparatus for selective adjustment of RF coil size for magnetic resonance imaging

Publications (3)

Publication Number Publication Date
EP0384061A2 true EP0384061A2 (fr) 1990-08-29
EP0384061A3 EP0384061A3 (fr) 1991-01-30
EP0384061B1 EP0384061B1 (fr) 1995-02-01

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EP89309341A Expired - Lifetime EP0384061B1 (fr) 1989-02-21 1989-09-14 Procédé et appareil pour l'ajustage sélectif de dimensions d'une bobine à haute fréquence pour l'imagerie par résonance magnétique

Country Status (5)

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US (1) US4897604A (fr)
EP (1) EP0384061B1 (fr)
JP (1) JPH0616761B2 (fr)
AT (1) ATE118099T1 (fr)
DE (1) DE68920990T2 (fr)

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DE4221759A1 (de) * 1991-10-11 1993-04-15 Hitachi Medical Corp Empfangsspulenvorrichtung fuer ein kernspintomographiegeraet
DE4318134A1 (de) * 1993-06-01 1994-12-08 Siemens Ag Zirkular polarisierende Lokalantenne
GB2319086A (en) * 1993-09-27 1998-05-13 British Tech Group Testing a sample by nuclear resonance
DE19730753A1 (de) * 1997-07-17 1999-01-21 Siemens Ag Halterung für eine flexible Oberflächenspule eines Magnetresonanzgerätes
EP0930510A3 (fr) * 1997-12-26 2001-04-11 Ge Yokogawa Medical Systems, Ltd. Bobine de détection pour appareil de diagnostic par résonance magnétique
US6268152B1 (en) 1993-06-25 2001-07-31 Affymetrix, Inc. Probe kit for identifying a base in a nucleic acid
DE102005002094A1 (de) * 2005-01-14 2006-07-27 Schleifring Und Apparatebau Gmbh HF - Spulen für Kernspintomographen
DE102005030745A1 (de) * 2005-06-29 2007-01-11 Schleifring Und Apparatebau Gmbh HF-Spulen für Kernspintomographen

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WO1991000528A1 (fr) * 1989-07-05 1991-01-10 MAX-PLANCK-Gesellschaft zur Förderung der Wissenschaften e.V. Sonde pour la tomographie a resonance magnetique nucleaire de tout le corps ou pour la spectroscopie a resonance magnetique nucleaire in-vivo localisee
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CN113759299A (zh) * 2021-09-29 2021-12-07 上海电气(集团)总公司智惠医疗装备分公司 一种头部线圈、核磁设备及调整方法

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Cited By (15)

* Cited by examiner, † Cited by third party
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DE4221759A1 (de) * 1991-10-11 1993-04-15 Hitachi Medical Corp Empfangsspulenvorrichtung fuer ein kernspintomographiegeraet
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DE68920990T2 (de) 1995-06-14
ATE118099T1 (de) 1995-02-15
EP0384061A3 (fr) 1991-01-30
US4897604A (en) 1990-01-30
JPH0616761B2 (ja) 1994-03-09
EP0384061B1 (fr) 1995-02-01
JPH02241434A (ja) 1990-09-26
DE68920990D1 (de) 1995-03-16

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